US4534357A - Multiple demodulation frequency Doppler - Google Patents
Multiple demodulation frequency Doppler Download PDFInfo
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- US4534357A US4534357A US06/601,815 US60181584A US4534357A US 4534357 A US4534357 A US 4534357A US 60181584 A US60181584 A US 60181584A US 4534357 A US4534357 A US 4534357A
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8979—Combined Doppler and pulse-echo imaging systems
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/02—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems using reflection of acoustic waves
- G01S15/50—Systems of measurement, based on relative movement of the target
- G01S15/58—Velocity or trajectory determination systems; Sense-of-movement determination systems
- G01S15/582—Velocity or trajectory determination systems; Sense-of-movement determination systems using transmission of interrupted pulse-modulated waves and based upon the Doppler effect resulting from movement of targets
- G01S15/584—Velocity or trajectory determination systems; Sense-of-movement determination systems using transmission of interrupted pulse-modulated waves and based upon the Doppler effect resulting from movement of targets with measures taken for suppressing velocity ambiguities, i.e. anti-aliasing
Definitions
- the present invention relates to medical ultrasound diagnostic equipment. In particular it relates to Doppler blood velocity meters.
- PRF pulse repetition frequency
- sample volume means the region of interest of blood flow velocity.
- sample volume and PRF are well known and understood in the art, and it is also well known that the maximum PRF which can be used without introducing depth ambiguities is equal to the speed of sound in the medium divided by twice the depth of the sample volume.
- aliasing A well recognized phenomenon, called "aliasing", wherein the blood flow appears to have a different velocity or direction than it actually has, occurs when blood flow exceeds a maximum velocity for a given ultrasound transmitted frequency. Aliasing results from the fact that the Doppler shift frequency is equal to twice the ultrasound transmitted frequency times the velocity of the moving blood divided by the velocity of sound in the body. When the Doppler frequency is more than one half the PRF, aliasing occurs. In other words, aliasing occurs when the maximum blood flow velocity is greater than or equal to the square of the speed of sound in the human body divided by eight times the ultrasound transmitted frequency times the sample volume depth. Accordingly, the maximum blood flow velocity which can be measured without exhibiting aliasing is inversely proportional to the sample volume depth in the body for a given ultrasound transmitted frequency.
- While one approach to increasing the maximum velocity which can be measured without aliasing is to reduce the frequency of the ultrasound transmitted energy, if the frequency decreases below about 2 MHz, the scattering phenomenon, which is required for observing the return Doppler signals, is degraded. In addition, a reduction in the ultrasound transmitted frequency also reduces the resolution of the sample volume. Accordingly, the approach of decreasing the frequency of the ultrasound transmitted frequency can be helpful to about 2 MHz. Thereafter, decreasing the ultrasound transmitted frequency has not been found to be a desirable approach to use for eliminating the aliasing effect. Accordingly, a new approach to providing an unaliased signal would be desirable.
- a new burst is not transmitted until the return from the location of interest, i.e. the sample volume, is received. If the velocity of sound in body tissue is c, then the time of flight, T, from the transducer to the sample volume depth, d, and back is:
- the detected Doppler shifted frequency, f d of a target moving with velocity, v, detected with carrier frequency, f 0 , is given by:
- PRF/2 is the highest frequency that can be measured without aliasing
- a broadband signal is transmitted.
- the Doppler shifted return is then detected at two different frequencies contained in the received wideband signal. If the mean frequency of each of the two signals is detected and the two are subtracted, the resulting frequency will be that which would have been produced by a system operating at the difference frequency.
- the detected Doppler shifted return frequencies produced would be:
- the detected Doppler frequency shift, f d is that which would have been produced by a Doppler system transmitting and demodulating at the difference frequency ⁇ f 0 (equal to f 2 -f 1 ). Since ⁇ f 0 can be made much smaller than f 1 or f 2 , f d will be proportionally smaller than f d1 or f d2 . Accordingly, the highest velocity that can be unambiguously detected is:
- FIG. 1 is a block diagram of the present invention
- FIG. 2 is a block diagram showing the manner of generating the sinusoidal wave used in FIG. 1;
- FIG. 3 is a frequency diagram showing the signals received by the present invention.
- the invention includes a standard Doppler system 12 (shown within dashed lines).
- the standard Doppler system 12 includes a master oscillator 14 and a transmitter 16 which transmits signals through a transducer 18. Signals received from the transducer 18 are passed through a receiver amplifier 20 and through a first multiplier 22 which multiplies the received signal by COS 2 ⁇ f 1 . The signal resulting from that multiplication goes through a low pass filter 24, a sample and hold circuit 26, and a high pass filter 28 into a mean frequency estimator 30.
- the received signals from receiver 20 are passed through a multiplier 32 which multiplies them by SIN 2 ⁇ f 1 and the resulting signal is then sent through a low pass filter 34, a sample and hold circuit 36, and a high pass filter 38 into the mean frequency estimator 30.
- the signals from the receiver 20 are also passed through a multiplier 42 where they are multiplied by COS 2 ⁇ f 2 . Those signals are then sent through a low pass filter 44, a sample and hold circuit 46, and a high pass filter 48 into a mean frequency estimator 50. Similarly, received signals from receiver 20 are multiplied in multiplier 52 by SIN 2 ⁇ f 2 and sent into a low pass filter 54, a sample and hold circuit 56, and a high pass filter 58 into a mean frequency estimator 50. The outputs of the mean frequency estimators 30, 50 are sent into a subtractor 60 to obtain the unaliased mean frequency on output line 90.
- FIG. 2 the method of generating the sinusoidal waves corresponding to COS 2 ⁇ f 1 , SIN 2 ⁇ f 1 , SIN 2 ⁇ f 2 , and COS 2 ⁇ f 2 on lines 23, 33, 53, and 43, respectively, are shown.
- outputs from the master oscillator 14 are sent through a divide-by-m circuit 74 to obtain a signal corresponding to 4f 2 on line 75, and into a divide-by-4 nmp circuit 86 to obtain a signal on line 88 which corresponds to PRF.
- the signal on line 63, corresponding to 4f 1 is sent through a series of flip flops 64, 66, 68 which are set up as divide-by-2 circuits in order to reduce their frequency down to f 1 for input into low pass filters 70, 72. It should be noted that since the signal going into low pass filter 70 comes from the Q output of flip flop 64 whereas the input signal into the low pass filter 72 comes from the NOT Q output of the flip flop 64, they are out of phase with respect to one another.
- the bandwidth of the signal transmitted is shown to include an area around the frequencies f 1 and f 2 . Accordingly, the detected Doppler frequency shift f d on line 90 (See FIG. 1) is what would have been produced by a Doppler system operating at the frequency difference ⁇ f 0 (equal to f 2 -f 1 ).
- ⁇ f 0 can be much smaller than f 1 or f 2
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Abstract
The device uses two Doppler receivers having different center frequencies. After the mean Doppler frequency of each receiver is determined, one of the mean Doppler frequencies is subtracted from the other one of the mean Doppler frequencies, thereby providing the mean Doppler frequency associated with a frequency which is equal to the difference between the two original frequencies. As this difference frequency is much lower than either of the two original frequencies, the resulting difference mean Doppler frequency will not be aliased
Description
The present invention relates to medical ultrasound diagnostic equipment. In particular it relates to Doppler blood velocity meters.
In the measurement of blood velocity using pulsed ultrasound Doppler equipment, there is a recognized problem in measuring the velocity of blood in deep lying vessels. The problem results from the fact that the pulse repetition frequency (hereinafter called "PRF") is determined, in part, by the depth within the body of the blood whose velocity is being measured. The PRF is typically selected such that a pulse can be transmitted from the transducer and reflected from blood flowing within the vessel with the return pulse being received prior to the transmission of the next succeeding pulse.
As used herein the term "sample volume" means the region of interest of blood flow velocity. The terms "sample volume" and "PRF" are well known and understood in the art, and it is also well known that the maximum PRF which can be used without introducing depth ambiguities is equal to the speed of sound in the medium divided by twice the depth of the sample volume.
A well recognized phenomenon, called "aliasing", wherein the blood flow appears to have a different velocity or direction than it actually has, occurs when blood flow exceeds a maximum velocity for a given ultrasound transmitted frequency. Aliasing results from the fact that the Doppler shift frequency is equal to twice the ultrasound transmitted frequency times the velocity of the moving blood divided by the velocity of sound in the body. When the Doppler frequency is more than one half the PRF, aliasing occurs. In other words, aliasing occurs when the maximum blood flow velocity is greater than or equal to the square of the speed of sound in the human body divided by eight times the ultrasound transmitted frequency times the sample volume depth. Accordingly, the maximum blood flow velocity which can be measured without exhibiting aliasing is inversely proportional to the sample volume depth in the body for a given ultrasound transmitted frequency.
While one approach to increasing the maximum velocity which can be measured without aliasing is to reduce the frequency of the ultrasound transmitted energy, if the frequency decreases below about 2 MHz, the scattering phenomenon, which is required for observing the return Doppler signals, is degraded. In addition, a reduction in the ultrasound transmitted frequency also reduces the resolution of the sample volume. Accordingly, the approach of decreasing the frequency of the ultrasound transmitted frequency can be helpful to about 2 MHz. Thereafter, decreasing the ultrasound transmitted frequency has not been found to be a desirable approach to use for eliminating the aliasing effect. Accordingly, a new approach to providing an unaliased signal would be desirable.
During normal operation of a pulsed Doppler system, a new burst is not transmitted until the return from the location of interest, i.e. the sample volume, is received. If the velocity of sound in body tissue is c, then the time of flight, T, from the transducer to the sample volume depth, d, and back is:
T=2d/c
Thus, the highest PRF that is normally used is:
PRF.sub.max =c/2d
The detected Doppler shifted frequency, fd, of a target moving with velocity, v, detected with carrier frequency, f0, is given by:
f.sub.d =2f.sub.0 v/c
As PRF/2 is the highest frequency that can be measured without aliasing,
f.sub.d =PRF/2=2f.sub.0 U.sub.max /c
Accordingly, the highest velocity, Umax, which can be unambiguously detected is:
U.sub.max =PRF*c/4f.sub.0 =(c.sup.2)/(8f.sub.0 d)
Heretofore, to prevent the problem of aliasing, either continuous wave Doppler was used, and all range resolution was lost, or, alternatively, the transmitted frequency was decreased. As noted above, decreasing the transmitted frequency only works down to a frequency of about 2 MHz due to decreased scattering. Increasing the PRF over PRFmax introduces range ambiguities, and tracking the mean frequency as a function of time requires knowledge that the signal is not aliased at some point in time as a reference and the knowledge that it does not change too rapidly. (See "Resolution of Frequency Aliases in Ultrasound Pulsed Doppler Velocimeters", Craig Hartley, IEEE Trans. Sonics and Ultrasonics, Vol. SU-28, 1981, pp 69-75.). All of the foregoing approaches sacrifice some significant aspect of pulsed Dopplers, such as range resolution, or, alternatively, they require that some assumptions be made which may not be valid.
In accordance with the present invention, a broadband signal is transmitted. The Doppler shifted return is then detected at two different frequencies contained in the received wideband signal. If the mean frequency of each of the two signals is detected and the two are subtracted, the resulting frequency will be that which would have been produced by a system operating at the difference frequency. Thus, for reference local oscillators which operate at frequencies f1 and f2, respectively, the detected Doppler shifted return frequencies produced would be:
f.sub.d1 =2vf.sub.1 /c,
and
f.sub.d2 =2vf.sub.2 /c
subtracting fd2 from fd1 gives:
f.sub.d =f.sub.d1 -f.sub.d2 =2v(f.sub.2 -f.sub.1)/c=2vΔf.sub.0 /c
Thus, the detected Doppler frequency shift, fd, is that which would have been produced by a Doppler system transmitting and demodulating at the difference frequency Δf0 (equal to f2 -f1). Since Δf0 can be made much smaller than f1 or f2, fd will be proportionally smaller than fd1 or fd2. Accordingly, the highest velocity that can be unambiguously detected is:
v.sub.max =c.sup.2 /(8Δf.sub.0 d)
If the frequencies are represented by binary numbers and binary arithmetic is used to perform the mean calculation in two's complement, so that (127/128)*(+PRF/2) is represented by 01111111 (within 1/128 for 8 bit resolution), and -PRF/2 is represented as 10,000,000, the calculation is very simple. The difference frequency is calculated by simply subtracting the two binary numbers using modulus arithmetic, and the resulting binary number represents the mean frequency as a fraction of PRF/2.
In the Drawing:
FIG. 1 is a block diagram of the present invention;
FIG. 2 is a block diagram showing the manner of generating the sinusoidal wave used in FIG. 1; and
FIG. 3 is a frequency diagram showing the signals received by the present invention.
Referring now to FIG. 1, the device 10 of the present invention is shown. The invention includes a standard Doppler system 12 (shown within dashed lines). The standard Doppler system 12 includes a master oscillator 14 and a transmitter 16 which transmits signals through a transducer 18. Signals received from the transducer 18 are passed through a receiver amplifier 20 and through a first multiplier 22 which multiplies the received signal by COS 2πf1. The signal resulting from that multiplication goes through a low pass filter 24, a sample and hold circuit 26, and a high pass filter 28 into a mean frequency estimator 30. Similarly, the received signals from receiver 20 are passed through a multiplier 32 which multiplies them by SIN 2πf1 and the resulting signal is then sent through a low pass filter 34, a sample and hold circuit 36, and a high pass filter 38 into the mean frequency estimator 30.
In accordance with the present invention, the signals from the receiver 20 are also passed through a multiplier 42 where they are multiplied by COS 2πf2. Those signals are then sent through a low pass filter 44, a sample and hold circuit 46, and a high pass filter 48 into a mean frequency estimator 50. Similarly, received signals from receiver 20 are multiplied in multiplier 52 by SIN 2πf2 and sent into a low pass filter 54, a sample and hold circuit 56, and a high pass filter 58 into a mean frequency estimator 50. The outputs of the mean frequency estimators 30, 50 are sent into a subtractor 60 to obtain the unaliased mean frequency on output line 90.
Referring now to FIG. 2, the method of generating the sinusoidal waves corresponding to COS 2πf1, SIN 2πf1, SIN 2πf2, and COS 2πf2 on lines 23, 33, 53, and 43, respectively, are shown. In particular, outputs from the master oscillator 14, which is made to oscillate at a frequency of 4 nmp×PRF, where n,m and p are integers, are sent into a divide-by-n circuit 62 to obtain an output frequency corresponding to 4f1 on a line 63. Similarly, outputs from the master oscillator 14 are sent through a divide-by-m circuit 74 to obtain a signal corresponding to 4f2 on line 75, and into a divide-by-4 nmp circuit 86 to obtain a signal on line 88 which corresponds to PRF. The signal on line 63, corresponding to 4f1 is sent through a series of flip flops 64, 66, 68 which are set up as divide-by-2 circuits in order to reduce their frequency down to f1 for input into low pass filters 70, 72. It should be noted that since the signal going into low pass filter 70 comes from the Q output of flip flop 64 whereas the input signal into the low pass filter 72 comes from the NOT Q output of the flip flop 64, they are out of phase with respect to one another. Accordingly, their outputs, on lines 23 and 33, respectively, correspond to COS 2πf1 and SIN 2πf1. Similarly, the outputs of low pass filters 82 and 84 correspond to SIN 2πf2 and COS 2πf2 on lines 53, 43.
With reference to FIG. 3, the bandwidth of the signal transmitted is shown to include an area around the frequencies f1 and f2. Accordingly, the detected Doppler frequency shift fd on line 90 (See FIG. 1) is what would have been produced by a Doppler system operating at the frequency difference Δf0 (equal to f2 -f1).
As noted above, since Δf0 can be much smaller than f1 or f2, fd will be proportionally smaller than fd1 or fd2. Accordingly, using the present invention, blood flow having a velocity of vmax =c2 /(8Δf0 d) can be detected.
Claims (3)
1. A multiple demodulation frequency Doppler detector for measuring the velocity of blood flowing in a patient's circulatory system comprising:
(a) a first Doppler system including a master oscillator operating at a master oscillator frequency, a transmitter, a transducer, and a receiver, and means for generating a first sine wave and a first cosine wave having a first frequency which is said master oscillator frequency divided by a first integer;
(b) a second Doppler system using said master oscillator, said transmitter, said transducer, and said receiver, and means for generating a second sine wave and a second cosine wave having a second frequency, different from said first frequency, said second frequency being said master oscillator frequency divided by a second integer different from said first integer;
(c) said first Doppler system further includes means for detecting the mean Doppler frequency of said first Doppler system using said first sine wave and said first cosine wave;
(d) said second Doppler system further includes means for detecting the mean Doppler frequency of said second Doppler system using said second sine wave and said second cosing wave; and
(e) means for detecting the difference between said mean Doppler frequency of said first and second Doppler signals, whereby said difference will be the unaliased mean Doppler frequency.
2. The multiple demodulation frequency Doppler detector of claim 1 wherein said means for generating a first sine wave and a first cosine wave having a first frequency which is said master oscillator frequency divided by a first integer comprises:
(a) a divide-by-n circuit, where n is an integer;
(b) at least one flip flop having complementary outputs; and
(c) low pass filter means associated with the complementary outputs of said flip flop.
3. The multiple demodulation frequency Doppler detector of claim 2 wherein said means for generating a second sine wave and a second cosine wave having a second frequency which is said master oscillator frequency divided by a second integer comprises:
(a) a divide-by-m circuit, where m is an integer;
(b) at least one flip flop having complementary outputs; and
(c) low pass filter means associated with the complementary outputs of said flip flop.
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| US06/601,815 US4534357A (en) | 1984-04-19 | 1984-04-19 | Multiple demodulation frequency Doppler |
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| US06/601,815 US4534357A (en) | 1984-04-19 | 1984-04-19 | Multiple demodulation frequency Doppler |
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Cited By (20)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0166392A2 (en) * | 1984-06-23 | 1986-01-02 | Aloka Co. Ltd. | Doppler signal frequency converter |
| EP0215137A1 (en) * | 1984-06-04 | 1987-03-25 | Dymax Corporation | Tissue signature tracking tranceiver |
| WO1988001850A1 (en) * | 1986-09-09 | 1988-03-24 | Vital Science Corporation | Method and apparatus for measuring volume fluid flow |
| DE3732399A1 (en) * | 1986-09-29 | 1988-04-07 | Toshiba Kawasaki Kk | ULTRASONIC BLOOD CURRENT MONITORING DEVICE |
| US4780837A (en) * | 1984-06-23 | 1988-10-25 | Aloka Co., Ltd. | Doppler signal frequency converter |
| US4817618A (en) * | 1985-05-30 | 1989-04-04 | Advanced Technology Laboratories, Inc. | Range-continuity anti-aliasing |
| EP0338592A1 (en) * | 1988-04-22 | 1989-10-25 | Matsushita Electric Industrial Co., Ltd. | An ultrasonic doppler blood flow velocity detection apparatus and a method for detecting blood flow velocity |
| EP0345960A1 (en) * | 1988-05-23 | 1989-12-13 | Matsushita Electric Industrial Co., Ltd. | An ultrasonic doppler blood flow velocity detection apparatus |
| EP0361945A2 (en) * | 1988-09-30 | 1990-04-04 | Shigeo Ohtsuki | Measuring doppler velocity |
| EP0362631A1 (en) * | 1988-10-03 | 1990-04-11 | Kontron Instruments Holding N.V. | Doppler flow rate meter |
| EP0441451A1 (en) * | 1990-02-09 | 1991-08-14 | Laboratoires D'electronique Philips S.A.S. | Echography device for measuring the velocity of moving organs and blood flow with high measurable speed limit |
| US5213104A (en) * | 1991-10-24 | 1993-05-25 | Reynolds Charles A | Doppler ultrasound monitor system |
| US5477858A (en) * | 1986-07-30 | 1995-12-26 | Siemens Medical Systems, Inc. | Ultrasound blood flow/tissue imaging system |
| US5891038A (en) * | 1996-12-30 | 1999-04-06 | General Electric Company | Method, apparatus and applications for combining transmit wave functions to obtain synthetic waveform in ultrasonic imaging system |
| US5961462A (en) * | 1998-05-18 | 1999-10-05 | Atl Ultrasound | Ultrasonic doppler imaging at high frame rates of display |
| US6179781B1 (en) * | 1999-03-31 | 2001-01-30 | Acuson Corporation | Medical diagnostic ultrasound method and apparatus for improving doppler processing |
| EP1079240A2 (en) * | 1999-08-23 | 2001-02-28 | GE Vingmed Ultrasound AS | Method and apparatus for providing real-time calculation and display of tissue deformation in ultrasound imaging |
| US6364838B1 (en) * | 2000-01-11 | 2002-04-02 | Siemens Medical Soulutions, Usa, Inc. | Pulsed wave doppler processing using aliased spectral data |
| US20030153831A1 (en) * | 2002-01-22 | 2003-08-14 | Jona Zumeris | System and method for detection of motion |
| US20070078347A1 (en) * | 2005-09-30 | 2007-04-05 | Siemens Medical Solutions Usa, Inc. | Ultrasound color flow imaging at high frame rates |
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| US3302161A (en) * | 1950-12-05 | 1967-01-31 | John V Ellison | Multiple-frequency ranging system |
| US3987673A (en) * | 1974-01-03 | 1976-10-26 | National Research Development Corporation | Ultrasonic transducer devices |
| US4453165A (en) * | 1983-01-03 | 1984-06-05 | Sperry Corporation | Differential Doppler receiver |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| US3302161A (en) * | 1950-12-05 | 1967-01-31 | John V Ellison | Multiple-frequency ranging system |
| US3987673A (en) * | 1974-01-03 | 1976-10-26 | National Research Development Corporation | Ultrasonic transducer devices |
| US4453165A (en) * | 1983-01-03 | 1984-06-05 | Sperry Corporation | Differential Doppler receiver |
Cited By (39)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0215137A1 (en) * | 1984-06-04 | 1987-03-25 | Dymax Corporation | Tissue signature tracking tranceiver |
| EP0166392A3 (en) * | 1984-06-23 | 1988-01-20 | Aloka Co. Ltd. | Doppler signal frequency converter |
| US4780837A (en) * | 1984-06-23 | 1988-10-25 | Aloka Co., Ltd. | Doppler signal frequency converter |
| EP0166392A2 (en) * | 1984-06-23 | 1986-01-02 | Aloka Co. Ltd. | Doppler signal frequency converter |
| US4817618A (en) * | 1985-05-30 | 1989-04-04 | Advanced Technology Laboratories, Inc. | Range-continuity anti-aliasing |
| US5477858A (en) * | 1986-07-30 | 1995-12-26 | Siemens Medical Systems, Inc. | Ultrasound blood flow/tissue imaging system |
| GB2213265B (en) * | 1986-09-09 | 1991-05-22 | Vital Science Corp | Method and apparatus for measuring volume fluid flow |
| WO1988001850A1 (en) * | 1986-09-09 | 1988-03-24 | Vital Science Corporation | Method and apparatus for measuring volume fluid flow |
| US4807636A (en) * | 1986-09-09 | 1989-02-28 | Vital Science Corporation | Method and apparatus for measuring volume fluid flow |
| GB2213265A (en) * | 1986-09-09 | 1989-08-09 | Vital Science Corp | Method and apparatus for measuring volume fluid flow |
| DE3732399A1 (en) * | 1986-09-29 | 1988-04-07 | Toshiba Kawasaki Kk | ULTRASONIC BLOOD CURRENT MONITORING DEVICE |
| US4794933A (en) * | 1986-09-29 | 1989-01-03 | Kabushiki Kaisha Toshiba | Ultrasonic blood stream observing apparatus |
| EP0338592A1 (en) * | 1988-04-22 | 1989-10-25 | Matsushita Electric Industrial Co., Ltd. | An ultrasonic doppler blood flow velocity detection apparatus and a method for detecting blood flow velocity |
| US4966153A (en) * | 1988-04-22 | 1990-10-30 | Matsushita Electric Industrial Co., Ltd. | Ultrasonic doppler blood flow velocity detection apparatus and a method for detecting blood flow velocity |
| US5035245A (en) * | 1988-05-23 | 1991-07-30 | Matsushita Electric Industrial Co., Ltd. | Ultrasonic Doppler blood flow velocity detection apparatus |
| EP0345960A1 (en) * | 1988-05-23 | 1989-12-13 | Matsushita Electric Industrial Co., Ltd. | An ultrasonic doppler blood flow velocity detection apparatus |
| EP0361945A3 (en) * | 1988-09-30 | 1991-04-24 | Shigeo Ohtsuki | Measuring doppler velocity |
| EP0361945A2 (en) * | 1988-09-30 | 1990-04-04 | Shigeo Ohtsuki | Measuring doppler velocity |
| EP0362631A1 (en) * | 1988-10-03 | 1990-04-11 | Kontron Instruments Holding N.V. | Doppler flow rate meter |
| US5046500A (en) * | 1988-10-03 | 1991-09-10 | Kontron Instruments Holding N.V. | Doppler flow velocity meter |
| EP0441451A1 (en) * | 1990-02-09 | 1991-08-14 | Laboratoires D'electronique Philips S.A.S. | Echography device for measuring the velocity of moving organs and blood flow with high measurable speed limit |
| FR2658069A1 (en) * | 1990-02-09 | 1991-08-16 | Philips Electronique Lab | DEVICE FOR MEASURING THE SPEED OF MOVING ORGANS AND BLOOD FLOWS BY ULTRASONIC ULTRASONIC ECHOGRAPHY, AT HIGH SPEED OF MEASUREMENT. |
| US5213104A (en) * | 1991-10-24 | 1993-05-25 | Reynolds Charles A | Doppler ultrasound monitor system |
| US5891038A (en) * | 1996-12-30 | 1999-04-06 | General Electric Company | Method, apparatus and applications for combining transmit wave functions to obtain synthetic waveform in ultrasonic imaging system |
| US5961462A (en) * | 1998-05-18 | 1999-10-05 | Atl Ultrasound | Ultrasonic doppler imaging at high frame rates of display |
| US6179781B1 (en) * | 1999-03-31 | 2001-01-30 | Acuson Corporation | Medical diagnostic ultrasound method and apparatus for improving doppler processing |
| US20040111027A1 (en) * | 1999-08-23 | 2004-06-10 | Hans Torp | Method and apparatus for providing real-time calculation and display of tissue deformation in ultrasound imaging |
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